Imaging system, methodology, and applications employing reciprocal space optical design

ABSTRACT

An imaging system, methodology, and various applications are provided to facilitate optical imaging performance. The system includes a sensor having one or more receptors and an image transfer medium to scale the sensor and receptors in accordance with resolvable characteristics of the medium. A computer, memory, and/or display associated with the sensor provides storage and/or display of information relating to output from the receptors to produce and/or process an image, wherein a plurality of illumination sources can also be utilized in conjunction with the image transfer medium.

RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 10/924,553 which was filed Aug. 24, 2004, entitled IMAGING SYSTEM, METHODOLOGY, AND APPLICATIONS EMPLOYING RECIPROCAL SPACE OPTICAL DESIGN, which is a continuation-in-part of U.S. patent application Ser. No. 10/758,739 which was filed Jan. 16, 2004, entitled IMAGING SYSTEM, METHODOLOGY, AND APPLICATIONS EMPLOYING RECIPROCAL SPACE OPTICAL DESIGN. This application is also a continuation-in-part of U.S. patent application Ser. No. 10/189,326 which was filed Jul. 2, 2002 entitled IMAGING SYSTEM AND METHODOLOGY EMPLOYING RECIPROCAL SPACE OPTICAL DESIGN, which is a continuation-in-part of U.S. patent application Ser. No. 09/900,218, which was filed Jul. 6, 2001, entitled IMAGING SYSTEM AND METHODOLOGY EMPLOYING RECIPROCAL SPACE OPTICAL DESIGN, all of which are incorporated herein by reference.

TECHNICAL FIELD

The present invention relates generally to image and optical systems, and more particularly to a system and method to facilitate imaging performance via an image transfer medium that projects characteristics of a sensor to an object field of view.

BACKGROUND OF THE INVENTION

Microscopes facilitate creating a large image of a tiny object. Greater magnification can be achieved if the light from an object is made to pass through two lenses compared to a simple microscope with one lens. A compound microscope has two or more converging lenses, placed in line with one another, so that both lenses refract the light in turn. The result is to produce an image that is magnified with improved quality in Resolved Magnification and other image parameters than either lens could alone. Light illuminating the object first passes through a short focal length lens or lens group, called the objective, and then travels on some distance before being passed through a longer focal length lens or lens group, called the eyepiece. A lens group is often simply referred to singularly as a lens. Usually these two lenses are held in paraxial relationship to one another, so that the axis of one lens is arranged to be in the same orientation as the axis of the second lens. It is the nature of the lenses, their properties, their relationship, and the relationship of the objective lens to the object that determines how a highly magnified image is produced in the eye of the observer.

The first lens or objective is usually a small lens with a very small focal length. A specimen or object is placed in the path of a light source with sufficient intensity to illuminate as desired. The objective lens is then lowered until the specimen is very close to, but not quite at the focal point of the lens. Light leaving the specimen and passing through the objective lens produces a real, inverted and magnified image behind the lens, in the microscope at a point generally referred to as the intermediate image plane. The second lens or eyepiece has a longer focal length and is placed in the microscope so that the image produced by the objective lens falls closer to the eyepiece than one focal length (that is, inside the focal point of the lens). The image from the objective lens now becomes the object for the eyepiece lens. As this object is inside one focal length, the second lens refracts the light in such a way as to produce a second image that is virtual, inverted and magnified. This is the final image seen by the eye of the observer.

Alternatively, common infinity space or infinity corrected design microscopes employ objective lenses with infinite conjugate properties such that the light leaving the objective is not focused, but is a flux of parallel rays which do not converge until after passing through a tube lens where the projected image is then located at the focal point of the eyepiece for magnification and observation. Many microscopes, such as the compound microscope described above, are designed to provide images of certain quality to the human eye through an eyepiece. Connecting a Machine Vision Sensor, such as a Charge Coupled Device (CCD) sensor, to the microscope so that an image may be viewed on a monitor presents difficulties. This is because the image quality provided by the sensor and viewed by a human eye decreases as compared to an image viewed by a human eye directly through an eyepiece. As a result, conventional optical systems for magnifying, observing, examining, and analyzing small items often require the careful attention of a technician monitoring the process through an eyepiece. It is for this reason, as well as others, that Machine-Vision or computer-based image displays from the aforementioned image sensor displayed on a monitor or other output display device are not of quality perceived by the human observer through the eyepiece.

SUMMARY OF THE INVENTION

The following presents a simplified summary of the invention in order to provide a basic understanding of some aspects of the invention. This summary is not an extensive overview of the invention. It is intended to neither identify key or critical elements of the invention nor delineate the scope of the invention. Its sole purpose is to present some concepts of the invention in a simplified form as a prelude to the more detailed description that is presented later.

The present invention relates to a system and methodology that facilitates imaging performance of optical imaging systems. In regard to several optical and/or imaging system parameters, many orders of performance enhancement can be realized over conventional systems (e.g., greater effective resolved magnification, larger working distances, increased absolute spatial resolution, increased spatial field of view, increased depth of field, Modulation Transfer Function of about 1, oil immersion objectives and eye pieces not required). This is achieved by adapting an image transfer medium (e.g., one or more lenses, fiber optical media, or other media) to a sensor having one or more receptors (e.g., pixels) such that the receptors of the sensor are effectively scaled (e.g., “mapped”, “sized”, “projected”, “matched”, “reduced”) to occupy an object field of view at about the scale or size associated with a diffraction limited point or spot within the object field of view. Thus, a band-pass filtering of spatial frequencies in what is known as Fourier space or “k-space” is achieved such that the projected size (projection in a direction from the sensor toward object space) of the receptor is filled in k-space.

In other words, the image transfer medium is adapted, configured and/or selected such that a transform into k-space is achieved, wherein an a priori design determination causes k-space or band-pass frequencies of interest to be substantially preserved throughout and frequencies above and below the k-space frequencies to be mitigated. It is noted that the frequencies above and below the k-space frequencies tend to cause blurring and contrast reduction and are generally associated with conventional optical system designs which define intrinsic constraints on a Modulation Transfer Function and “optical noise”. This further illustrates that the systems and methods of the present invention are in contravention or opposition to conventional geometric paraxial ray designs. Consequently, many known optical design limitations associated with conventional systems are mitigated by the present invention.

According to one aspect of the present invention, a “k-space” design, system and methodology is provided which defines a “unit-mapping” of the Modulation Transfer Function (MTF) of an object plane to image plane relationship. The k-space design projects image plane pixels or receptors forward to the object plane to promote an optimum theoretical relationship. This is defined by a substantially one-to-one correspondence between image sensor receptors and projected object plane units (e.g., units defined by smallest resolvable points or spots in an optical or image transfer medium) that are matched according to the receptor size. The k-Space design defines that “unit-mapping” or “unit-matching” acts as an effective “Intrinsic Spatial Filter” which implies that spectral components of both an object and an image in k-space (also referred to as “reciprocal-space”) are substantially matched or quantized. Advantages provided by the k-space design result in a system and methodology capable of much higher effective resolved magnification with concomitantly related and much increased Field Of View, Depth Of Field, Absolute Spatial Resolution, and Working Distances utilizing dry objective lens imaging, for example, and without employing conventional oil immersion techniques having inherent intrinsic limitations to the aforementioned parameters.

One aspect of the present invention relates to an optical system that includes an optical sensor having an array of light receptors having a pixel pitch. A lens optically associated with the optical sensor is configured with optical parameters functionally related to the pitch and a desired resolution of the optical system. As a result, the lens is operative to substantially map a portion of an object having the desired resolution along the optical path to an associated one of the light receptors.

Another aspect of the present invention relates to a method of designing an optical system. The method includes selecting a sensor with a plurality of light receptors having a pixel pitch. A desired minimum spot size resolution is selected for the system and a lens configured or an extant lens selected with optical parameters based on the pixel pitch and the desired minimum spot size is provided so as to map the plurality of light receptors to part of the image according to the desired resolution.

The present invention can be employed in various portable, stand-alone, or a combination of portable and stand-alone applications. For example, this can include portable imaging systems that can be distributed throughout the world to support various remote imaging applications. Such applications can include remote medicine or industrial applications whereby an image is generated in one location and transmitted to another location for analysis (e.g., remote pathology application).

The following description and the annexed drawings set forth in detail certain illustrative aspects of the invention. These aspects are indicative, however, of but a few of the various ways in which the principles of the invention may be employed and the present invention is intended to include all such aspects and their equivalents. Other advantages and novel features of the invention will become apparent from the following detailed description of the invention when considered in conjunction with the drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic block diagram illustrating an imaging system in accordance with an aspect of the present invention.

FIG. 2 is a diagram illustrating a k-space system design in accordance with an aspect of the present invention.

FIG. 3 is a diagram of an exemplary system illustrating sensor receptor matching in accordance with an aspect of the present invention.

FIG. 4 is a graph illustrating sensor matching considerations in accordance with an aspect of the present invention.

FIG. 5 is a graph illustrating a Modulation Transfer Function in accordance with an aspect of the present invention.

FIG. 6 is a graph illustrating a figure of merit relating to a Spatial Field Number in accordance with an aspect of the present invention.

FIG. 7 is a flow diagram illustrating an imaging methodology in accordance with an aspect of the present invention.

FIG. 8 is a flow diagram illustrating a methodology for selecting optical parameters in accordance with an aspect of the present invention.

FIGS. 9-17 illustrate various exemplary imaging designs in accordance with an aspect of the present invention.

FIG. 18 illustrates an excitation application in accordance with an aspect of the present invention.

FIGS. 19 and 20 illustrate beam-scanning technologies that can be applied to increase excitation yields in accordance with an aspect of the present invention.

FIG. 21 illustrates an example system for integrating or retrofitting pixel-mapping components in accordance with an aspect of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

The present invention relates to an optical and/or imaging system and methodology. According to one aspect of the present invention, a k-space filter is provided that can be configured from an image transfer medium such as optical media that correlates image sensor receptors to an optical or image transfer medium. A variety of illumination sources can also be employed to achieve one or more operational goals and for versatility of application. The k-space design of the imaging system of the present invention promotes capture and analysis (e.g., automated and/or manual) of images having a high Field Of View (FOV) at substantially high Effective Resolved Magnification as compared to conventional systems. This can include employing a small Numerical Aperture (NA) associated with lower magnification objective lenses to achieve very high Effective Resolved Magnification. As a consequence, images having a substantially large Depth Of Field (DOF) at very high Effective Resolved Magnification are also realized. The k-space design also facilitates employment of homogeneous illumination sources that are substantially insensitive to changes in position, thereby improving methods of examination and analysis.

According to another aspect of the present invention, an objective lens to object distance (e.g., Working Distance) can be maintained in operation at low and high power effective resolved magnification imaging, wherein typical spacing can be achieved at about 0.1 mm or more and about 20 mm or less, as opposed to conventional microscopic systems which can require significantly smaller (as small as 0.01 mm) object to objective lens distances for comparable (e.g., similar order of magnitude) Effective Resolved Magnification values. In another aspect, the Working Distance is about 0.5 mm or more and about 10 mm or less. It is to be appreciated that the present invention is not limited to operating at the above working distances. In many instances the above working distances are employed, however, in some instances, smaller or larger distances are employed. It is further noted that oil immersion or other Index of Refraction matching media or fluids for objective lenses are generally not required (e.g., substantially no improvement to be gained) at one or more effective image magnification levels of the present invention yet, still exceeding effective resolved magnification levels achievable in conventional microscopic optical design variations including systems employing “infinity-corrected” objective lenses.

The k-space design of the present invention defines that a small “Blur Circle” or diffraction limited point/spot at the object plane is determined by parameters of the design to match image sensor receptors or pixels with a substantially one-to-one correspondence by “unit-mapping” of object and image spaces for associated object and image fields. This enables the improved performance and capabilities of the present invention. One possible theory of the k-space design results from the mathematical concept that since the Fourier Transform of both an object and an image is formed in k-space (also called “reciprocal space”), the sensor should be mapped to the object plane in k-space via optical design techniques and component placement in accordance with the present invention. It is to be appreciated that a plurality of other transforms or models can be utilized to configure and/or select one or more components in accordance with the present invention. For example, wavelet transforms, Laplace (s-transforms), z-transforms as well as other transforms can be similarly employed.

The k-space design methodology is unlike conventional optical systems designed according to geometric, paraxial ray-trace and optimization theory, since the k-space optimization facilitates that the spectral components of the object (e.g., tissue sample, particle, semiconductor) and the image are the same in k-space, and thus quantized. Therefore, there are substantially no inherent limitations imposed on a Modulation Transfer Function (MTF) describing contrast versus resolution and absolute spatial resolution in the present invention. Quantization, for example, in k-space yields a substantially unitary Modulation Transfer Function not realized by conventional systems. It is noted that high MTF, Spatial Resolution, and effective resolved image magnification can be achieved with much lower magnification objective lenses with desirable lower Numerical Apertures (e.g., generally less than about 50× with a numerical aperture of generally less than about 0.7) through “unit-mapping” of projected pixels in an “Intrinsic Spatial Filter” provided by the k-space design.

If desired, “infinity-corrected” objectives can be employed with associated optical component and illumination, as well as spectrum varying components, polarization varying components, and/or contrast or phase varying components. These components can be included in an optical path-length between an objective and the image lens within an “infinity space”. Optical system accessories and variations can thus be positioned as interchangeable modules in this geometry. The k-space design, in contrast to conventional microscopic imagers that utilize “infinity-corrected” objectives, enables the maximum optimization of the infinity space geometry by the “unit-mapping” concept. This implies that there is generally no specific limit to the number of additional components that can be inserted in the “infinity space” geometry as in conventional microscopic systems that typically specify no more than 2 additional components without optical correction.

The present invention also enables a “base-module” design that can be configured and reconfigured in operation for a plurality of different applications if necessary to employ transmissive and/or reflected illumination, if desired. This includes substantially all typical machine vision illumination schemes (e.g., darkfield, brightfield, phase-contrast), and other microscopic transmissive techniques (Kohler, Abbe), in substantially any offset and can include Epi-illumination—and variants thereof. The systems of the present invention can be employed in a plurality of opto-mechanical designs that are robust since the k-space design is substantially not sensitive to environmental and mechanical vibration and thus generally does not require heavy structural mechanical design and isolation from vibration associated with conventional microscopic imaging instruments. Other features can include digital image processing, if desired, along with storage (e.g., local database, image data transmissions to remote computers for storage/analysis) and display of the images produced in accordance with the present invention (e.g., computer display, printer, film, and other output media). Remote signal processing of image data can be provided, along with communication and display of the image data via associated data packets that are communicated over a network or other medium, for example.

Moreover, images that are created in accordance with the present invention can be stored and/or transmitted with other digital information (e.g., audio data, other images, medical histories, product information, analysis information, and so forth). For example, an image may have associated voice-encoded data describing one or more aspects of the image or images contained as part of a data package that can be stored locally and/or transmitted across a network for remote storage and/or further analysis. In one specific example, an image created in accordance with the present invention can be transmitted to a remote location, wherein the image is further analyzed (e.g., medical or product specialist analyzes received image on a computer or image display). After analysis, a voice encoding or related data is appended or encoded with the received image and then transmitted back to the originating location (or other location), wherein the image and resultant encoded analysis can be reviewed. As can be appreciated, substantially any type of digital information can be stored and/or transmitted with images that are created in accordance with the present invention.

Also, as will be apparent from the following description, the present invention can be economically implemented in a plurality of various packages including integrated imaging/computing systems that are employed to analyze various samples. Such systems include handheld devices, notebook computers, laptops, personal digital assistants, and so forth that are adapted with the imaging concepts described herein.

Referring initially to FIG. 1, an imaging system 10 is illustrated in accordance with an aspect of the present invention. The imaging system 10 includes a sensor 20 having one or more receptors such as pixels or discrete light detectors (See e.g., illustrated below in FIG. 3) operably associated with an image transfer medium 30. The image transfer medium 30 is adapted or configured to scale the proportions of the sensor 20 at an image plane established by the position of the sensor 20 to an object field of view illustrated at reference numeral 34. A planar reference 36 of X and Y coordinates is provided to illustrate the scaling or reduction of the apparent or virtual size of the sensor 20 to the object field of view 34. Direction arrows 38 and 40 illustrate the direction of reduction of the apparent size of the sensor 20 toward the object field of view 34.

The object field of view 34 established by the image transfer medium 30 is related to the position of an object plane 42 that includes one or more items under microscopic examination (not shown). It is noted that the sensor 20 can be substantially any size, shape and/or technology (e.g., digital sensor, analog sensor, Charge Coupled Device (CCD) sensor, CMOS sensor, Charge Injection Device (CID) sensor, an array sensor, a linear scan sensor) including one or more receptors of various sizes and shapes, the one or more receptors being similarly sized or proportioned on a respective sensor to be responsive to light (e.g., visible, non-visible, “light”, “radiation”, or other such “visible” or “invisible” or “non-visible” hereafter meaning radiation of some desired wavelength optically directed. That is: radiation of any particular wavelength whose optical path, direction, and/or path length is altered by means of an optical medium, surface, material, component, or components, or other such means suitable to radiation of that wavelength in the configuration or configurations pertaining to the direction of such radiation to achieve the desired characteristics in accordance with the present invention) received from the items under examination in the object field of view 34.

As light is received from the object field of view 34, the sensor 20 provides an output 44 that can be directed to a local or remote storage such as a memory (not shown) and displayed from the memory via a computer and associated display, for example, without substantially any intervening digital processing (e.g., straight bit map from sensor memory to display), if desired. It is noted that local or remote signal processing of the image data received from the sensor 20 can also occur. For example, the output 44 can be converted to electronic data packets and transmitted to a remote system over a network and/or via wireless transmissions systems and protocols for further analysis and/or display. Similarly, the output 44 can be stored in a local computer memory before being transmitted to a subsequent computing system for further analysis and/or display.

The scaling provided by the image transfer medium 30 is determined by a novel k-space configuration or design within the medium that promotes predetermined k-space frequencies of interest and mitigates frequencies outside the predetermined frequencies. This has the effect of a band-pass filter of the spatial frequencies within the image transfer medium 30 and notably defines the imaging system 10 in terms of resolution rather than magnification. As will be described in more detail below, the resolution of the imaging system 10 determined by the k-space design promotes a plurality of features in a displayed or stored image such as having high effective resolved magnification, high absolute spatial resolution, large depth of field, larger working distances, and a unitary Modulation Transfer Function as well as other features.

In order to determine the k-space frequencies, a “pitch” or spacing is determined between adjacent receptors on the sensor 20, the pitch related to the center-to-center distance of adjacent receptors and about the size or diameter of a single receptor. The pitch of the sensor 20 defines the Nyquist “cut-off” frequency band of the sensor. It is this frequency band that is promoted by the k-space design, whereas other frequencies are mitigated. In order to illustrate how scaling is determined in the imaging system 10, a small or diffraction limited spot or point 50 is illustrated at the object plane 42. The diffraction limited point 50 represents the smallest resolvable object determined by optical characteristics within the image transfer medium 30 and is described in more detail below. A scaled receptor 54, depicted in front of the field of view 34 for exemplary purposes, and having a size determined according to the pitch of the sensor 20, is matched or scaled to be about the same size in the object field of view 34 as the diffraction limited point 50 which is a function of the resolvable characteristics of the image transfer medium 30.

In other words, the size of any given receptor at the sensor 20 is effectively reduced in size via the image transfer medium 30 to be about the same size (or matched in size) to the size of the diffraction limited point 50. This also has the effect of filling the object field of view 34 with substantially all of the receptors of the sensor 20, the respective receptors being suitably scaled to be similar in size to the diffraction limited point 50. As will be described in more detail below, the matching/mapping of sensor characteristics to the smallest resolvable object or point within the object field of view 34 defines the imaging system 10 in terms of absolute spatial resolution and thus, enhances the operating performance of the system.

An illumination source 60 can be provided with the present invention in order that photons from the source can be transmitted through and/or reflected from objects in the field of view 34 to enable activation of the receptors in the sensor 20. It is noted that the present invention can potentially be employed without an illumination source 60 if potential self-luminous objects (e.g., fluorescent or phosphorescent biological or organic material sample, metallurgical, mineral, and/or other inorganic material and so forth) emit enough radiation to activate the sensor 60. Light Emitting Diodes, however, provide an effective illumination source 60 in accordance with the present invention. Substantially any illumination source 60 can be applied including coherent and non-coherent sources, visible and non-visible wavelengths. However, for non-visible wavelength sources, the sensor 20 and if necessary, the optical media of the image transfer medium 30 would also be suitably adapted. For example, for an infrared or ultraviolet source, an infrared or ultraviolet sensor 20 and IR or UV suitable optical components in the image transfer medium 30 would be employed, respectively. Other illumination sources 60 can include wavelength-specific lighting, broad-band lighting, continuous lighting, strobed lighting, Kohler illumination, Abbe illumination, phase-contrast illumination, darkfield illumination, brightfield illumination, and Epi illumination. Transmissive or reflective lighting techniques (e.g., specular and diffuse) can also be applied.

Reference numeral 80 depicts the outline of an image transfer medium, associated sensor, and computer system which receives image data from the associated sensor for generating images in accordance with the present invention. It is to be appreciated that these components can be configured in a plurality of different combinations such as in various portable configurations (e.g., hand held or laptop device), stand-alone configurations (e.g., industrial analyzer), or a combination of portable and stand-alone configurations/applications. For example, these configurations can include a plurality of portable imaging systems that may be powered by portable power sources, generators, batteries, solar, fuel-cell, other power sources which offer power appropriate to both the imaging system and the associated computer and display system, and can be distributed throughout differing regions to support various remote imaging applications. Such applications can include remote medicine or remote industrial applications whereby images are generated in one or more locations and transmitted to another location or location for analysis (e.g., remote pathology application, semiconductor quality control application).

Referring now to FIG. 2, a system 100 illustrates an image transfer medium in accordance with an aspect of the present invention. The image transfer medium 30 depicted in FIG. 1 can be provided according to the k-space design concepts described above and more particularly via a k-space filter 110 adapted, configured and/or selected to promote a band of predetermined k-space frequencies 114 and to mitigate frequencies outside of this band. This is achieved by determining a pitch “P”—which is the distance between adjacent receptors 116 in a sensor (not shown) and sizing optical media within the filter 110 such that the pitch “P” of the receptors 116 is matched in size with a diffraction-limited spot 120. The diffraction-limited spot 120 can be determined from the optical characteristics of the media in the filter 110. For example, the Numerical Aperture of an optical medium such as a lens defines the smallest object or spot that can be resolved by the lens. The filter 110 performs a k-space transformation such that the size of the pitch is effectively matched, “unit-mapped”, projected, correlated, and/or reduced to the size or scale of the diffraction limited spot 120.

It is to be appreciated that a plurality of optical configurations can be provided to achieve the k-space filter 110. One such configuration can be provided by an aspherical lens 124 adapted such to perform the k-space transformation and reduction from sensor space to object space. Yet another configuration can be provided by a multiple lens arrangement 128, wherein the lens combination is selected to provide the filtering and scaling. Still yet another configuration can employ a fiber optic taper 132 or image conduit, wherein multiple optical fibers or array of fibers are configured in a funnel-shape to perform the mapping of the sensor to the object field of view. It is noted that the fiber optic taper 132 is generally in physical contact between the sensor and the object under examination (e.g., contact with microscope slide). Another possible k-space filter 110 arrangement employs a holographic (or other diffractive or phase structure) optical element 136, wherein a substantially flat optical surface is configured via a hologram (or other diffractive or phase structure) (e.g., computer-generated, optically generated, and/or other method) to provide the mapping in accordance with the present invention.

The k-space optical design as enabled by the k-space filter 110 is based upon the “effective projected pixel-pitch” of the sensor, which is a figure derived from following (“projecting”) the physical size of the sensor array elements back through the optical system to the object plane. In this manner, conjugate planes and optical transform spaces are matched to the Nyquist cut-off of the effective receptor or pixel size. This maximizes the effective resolved image magnification and the Field Of View as well as the Depth Of Field and the Absolute Spatial Resolution. Thus, a novel application of optical theory is provided that does not rely on conventional geometric optical design parameters of paraxial ray-tracing which govern conventional optics and imaging combinations. This can further be described in the following manner.

A Fourier transform of an object and an image is formed (by an optical system) in k-space (also referred to as “reciprocal-space”). It is this transform that is operated on for image optimization by the k-space design of the present invention. For example, the optical media employed in the present invention can be designed with standard, relatively non-expensive “off-the-shelf” components having a configuration which defines that the object and image space are “unit-mapped” or “unit-matched” for substantially all image and object fields. A small Blur-circle or diffraction-limited spot 120 at the object plane is defined by the design to match the pixels in the image plane (e.g., at the image sensor of choice) with substantially one-to-one correspondence and thus the Fourier transforms of pixelated arrays can be matched. This implies that, optically by design, the Blur-circle is scaled to be about the same size as the receptor or pixel pitch. The present invention is defined such that it constructs an Intrinsic Spatial Filter such as the k-space filter 110. Such a design definition and implementation enables the spectral components of both the object and the image in k-space to be about the same or quantized. This also defines that the Modulation Transfer Function (MTF) (the comparison of contrast to spatial resolution) of the sensor is matched to the MTF of the object Plane.

FIG. 3 illustrates an optical system 200 in accordance with an aspect of the present invention. The system 200 includes a sensor 212 having a plurality of receptors or sensor pixels 214. For example, the sensor 212 is an M by N array of sensor pixels 214, having M rows and N columns (e.g., 640×480, 512×512, 1280×1024, and so forth), M and N being integers respectively. Although a rectangular sensor 212 having generally square pixels is depicted, it is to be understood and appreciated that the sensor can be substantially any shape (e.g., circular, elliptical, hexagonal, rectangular, and so forth). It is to be further appreciated that respective pixels 214 within the array can also be substantially any shape or size, the pixels in any given array 212 being similarly sized and shaped in accordance with an aspect of the present invention.

The sensor 212 can be substantially any technology (e.g., digital sensor, analog sensor, Charge Coupled Device (CCD) sensor, CMOS sensor, Charge Injection Device (CID) sensor, an array sensor, a linear scan sensor) including one or more receptors (or pixels) 214. According to one aspect of the present invention, each of the pixels 214 is similarly sized or proportioned and responsive to light (e.g., visible, non-visible) received from the items under examination, as described herein.

The sensor 212 is associated with a lens network 216, which is configured based on performance requirements of the optical system and the pitch size of sensor 212. The lens network 216 is operative to scale (or project) proportions (e.g., pixels 214) of the sensor 212 at an image plane established by the position of the sensor 212 to an object field of view 220 in accordance with an aspect of the present invention. The object field of view 220 is related to the position of an object plane 222 that includes one or more items (not shown) under examination.

As the sensor 212 receives light from the object field of view 220, the sensor 212 provides an output 226 that can be directed to a local or remote storage such as a memory (not shown) and displayed from the memory via a computer and associated display, for example, without substantially any intervening digital processing (e.g., straight bit map from sensor memory to display), if desired. It is noted that local or remote signal processing of the image data received from the sensor 212 can also occur. For example, the output 226 can be converted to electronic data packets and transmitted to a remote system over a network for further analysis and/or display. Similarly, the output 226 can be stored in a local computer memory before being transmitted to a subsequent computing system for further analysis and/or display.

The scaling (or effective projecting) of pixels 214 provided by the lens network 216 is determined by a novel k-space configuration or design in accordance with an aspect of the present invention. The k-space design of the lens network 216 promotes predetermined k-space frequencies of interest and mitigates frequencies outside the predetermined frequency band. This has the effect of a band-pass filter of the spatial frequencies within the lens network 216 and notably defines the imaging system 200 in terms of resolution rather than magnification. As will be described below, the resolution of the imaging system 200 determined by the k-space design promotes a plurality of features in a displayed or stored image, such as having high “Effective Resolved Magnification” (a figure of merit described in following), with related high absolute spatial resolution, large depth of field, larger working distances, and a unitary Modulation Transfer Function as well as other features.

In order to determine the k-space frequencies, a “pitch” or spacing 228 is determined between adjacent receptors 214 on the sensor 212. The pitch (e.g., pixel pitch) corresponds to the center-to-center distance of adjacent receptors, indicated at 228, which is about the size or diameter of a single receptor when the sensor includes all equally sized pixels. The pitch 228 defines the Nyquist “cut-off” frequency band of the sensor 212. It is this frequency band that is promoted by the k-space design, whereas other frequencies are mitigated. In order to illustrate how scaling is determined in the imaging system 200, a point 230 of a desired smallest resolvable spot size is illustrated at the object plane 222, wherein the point is derived from resolvable characteristics of the lens network 216. The point 230, for example, can represent the smallest resolvable object determined by optical characteristics of the lens network 216. That is, the lens network is configured to have optical characteristics (e.g., magnification, numerical aperture) so that respective pixels 214 are matched or scaled to be about the same size in the object field of view 220 as the desired minimum resolvable spot size of the point 230. For purposes of illustration, a scaled receptor 232 is depicted in front of the field of view 220 as having a size determined according to the pitch 228 of the sensor 212, which is about the same as the point 230.

By way of illustration, the lens network 216 is designed to effectively reduce the size of each given receptor (e.g., pixel) 214 at the sensor 212 to be about the same size (e.g., matched in size) to the size of the point 230, which is typically the minimum spot size resolvable by the system 210. It is to be understood and appreciated that the point 230 can be selected to a size representing the smallest resolvable object determined by optical characteristics within the lens network 216 as determined by diffraction rules (e.g., diffraction limited spot size). The lens network 216 thus can be designed to effectively scale each pixel 214 of the sensor 212 to any size that is equal to or greater than the diffraction limited size. For example, the resolvable spot size can be selected to provide for any desired image resolution that meets such criteria.

After the desired resolution (resolvable spot size) is selected, the lens network 216 is designed to provide the magnification to scale the pixels 214 to the object field of view 220 accordingly. This has the effect of filling the object field of view 220 with substantially all of the receptors of the sensor 212, the respective receptors being suitably scaled to be similar in size to the point 230, which corresponds to the desired resolvable spot size. The matching/mapping of sensor characteristics to the desired (e.g., smallest) resolvable object or point 230 within the object field of view 220 defines the imaging system 200 in terms of absolute spatial resolution and enhances the operating performance of the system in accordance with an aspect of the present invention.

By way of further illustration, in order to provide unit-mapping according to this example, assume that the sensor array 212 provides a pixel pitch 228 of about 10.0 microns. The lens network 216 includes an objective lens 234 and a secondary lens 236. For example, the objective lens 234 can be set at infinite conjugate to the secondary lens 236, with the spacing between the objective and secondary lenses being flexible. The lenses 234 and 236 are related to each other so as to achieve a reduction from sensor space defined at the sensor array 220 to object space defined at the object plane 222. It is noted that substantially all of the pixels 214 are projected into the object field of view 220, which is defined by the objective lens 234. For example, the respective pixels 214 are scaled through the objective lens 234 to about the dimensions of the desired minimum resolvable spot size. In this example, the desired resolution at the image plane 222 is one micron. Thus, a magnification of ten times is operative to back project a ten micron pixel to the object plane 222 and reduce it to a size of one micron.

The reduction in size of the array 212 and associated pixels 214 can be achieved by selecting the transfer lens 236 to have a focal length “D2” (from the array 212 to the transfer lens 236) of about 150 millimeters and by selecting the objective lens to have a focal length “D1” (from the objective lens 236 to the object plane 222) of about 15 millimeters, for example. In this manner, the pixels 214 are effectively reduced in size to about 1.0 micron per pixel, thus matching the size of the of the desired resolvable spot 230 and filling the object field of view 220 with a “virtually-reduced” array of pixels. It is to be understood and appreciated that other arrangements of one or more lenses can be employed to provide the desired scaling.

In view of the foregoing description, those skilled in the art will understand and appreciate that the optical media (e.g., lens network 216) can be designed, in accordance with an aspect of the present invention, with standard, relatively inexpensive “off-the-shelf” components having a configuration that defines that the object and image space are “unit-mapped” or “unit-matched” for substantially all image and object fields. The lens network 216 and, in particular the objective lens 234, performs a Fourier transform of an object and an image in k-space (also referred to as “reciprocal-space”). It is this transform that is operated on for image optimization by the k-space design of the present invention.

A small Blur-circle or Airy disk at the object plane is defined by the design to match the pixels in the image plane (e.g., at the image sensor of choice) with substantially one-to-one correspondence with the Airy disk and thus the Fourier transforms of pixilated arrays can be matched. This implies that, optically by design, the Airy disk is scaled through the lens network 216 to be about the same size as the receptor or pixel pitch. As mentioned above, the lens network 216 is defined so as to construct an Intrinsic Spatial Filter (e.g., a k-space filter). Such a design definition and implementation enables the spectral components of both the object and the image in k-space to be about the same or quantized. This also defines that a Modulation Transfer Function (MTF) (the comparison of contrast to spatial resolution) of the sensor can be matched to the MTF of the object Plane in accordance with an aspect of the present invention.

As illustrated in FIG. 3, k-space is defined as the region between the objective lens 234 and the secondary lens 236. It is to be appreciated that substantially any optical media, lens type and/or lens combination that reduces, maps and/or projects the sensor array 212 to the object field of view 220 in accordance with unit or k-space mapping as described herein is within the scope of the present invention.

To illustrate the novelty of the exemplary lens/sensor combination depicted in FIG. 3, it is noted that conventional objective lenses, sized according to conventional geometric paraxial ray techniques, are generally sized according to the magnification, Numeric Aperture, focal length and other parameters provided by the objective. Thus, the objective lens would be sized with a greater focal length than subsequent lenses that approach or are closer to the sensor (or eyepiece in conventional microscope) in order to provide magnification of small objects. This can result in magnification of the small objects at the object plane being projected as a magnified image of the objects across “portions” of the sensor and results in known detail blur (e.g., Rayleigh diffraction and other limitations in the optics), empty magnification problems, and Nyquist aliasing among other problems at the sensor. The k-space design of the present invention operates in an alternative manner to conventional geometrical paraxial ray design principles. That is, the objective lens 234 and the secondary lens 236 operate to provide a reduction in size of the sensor array 212 to the object field of view 220, as demonstrated by the relationship of the lenses.

An illumination source 240 can be provided with the present invention in order that photons from that source can be transmitted through and/or reflected from objects in the field of view 234 to enable activation of the receptors in the sensor 212. It is noted that the present invention can potentially be employed without an illumination source 240 if potential self-luminous objects (e.g., objects or specimens with emissive characteristics as previously described) emit enough radiation to activate the sensor 212. Substantially any illumination source 240 can be applied including coherent and non-coherent sources, visible and non-visible wavelengths. However, for non-visible wavelength sources, the sensor 212 would also be suitably adapted. For example, for an infrared or ultraviolet source, an infrared or ultraviolet sensor 212 would be employed, respectively. Other suitable illumination sources 240 can include wavelength-specific lighting, broad-band lighting, continuous lighting, strobed lighting, Kohler illumination, Abbe illumination, phase-contrast illumination, darkfield illumination, brightfield illumination, Epi illumination, and the like. Transmissive or reflective (e.g., specular and diffuse) lighting techniques can also be applied.

FIG. 4 illustrates a graph 300 of mapping characteristics and comparison between projected pixel size on the X-axis and diffraction-limited spot resolution size “R” on the Y-axis. An apex 310 of the graph 300 corresponds to unit mapping between projected pixel size and the diffraction limited spot size, which represents an optimum relationship between a lens network and a sensor in accordance with the present invention.

It is to be appreciated that the objective lens 234 (FIG. 3) should generally not be selected such that the diffraction-limited size “R” of the smallest resolvable objects are smaller than a projected pixel size. If so, “economic waste” can occur wherein more precise information is lost (e.g., selecting an object lens more expensive than required, such as having a higher numerical aperture). This is illustrated to the right of a dividing line 320 at reference 330 depicting a projected pixel 340 larger that two smaller diffraction spots 350. In contrast, where an objective is selected with diffraction-limited performance larger than the projected pixel size, blurring and empty magnification can occur. This is illustrated to the left of line 320 at reference numeral 360, wherein a projected pixel 370 is smaller than a diffraction-limited object 380. It is to be appreciated, however, that even if substantially one-to-one correspondence is not achieved between projected pixel size and the diffraction-limited spot, a system can be configured with less than optimum matching (e.g., 0.1%, 1%, 2%, 5%, 20%, 95% down from the apex 310 on the graph 300 to the left or right of the line 320) and still provide suitable performance in accordance with an aspect of the present invention. Thus, less than optimal matching is intended to fall within the spirit and the scope of present invention.

It is further to be appreciated that the diameter of the lenses in the system as illustrated in FIG. 3, for example, should be sized such that when a Fourier Transform is performed from object space to sensor space, spatial frequencies of interest that are in the band pass region described above (e.g., frequencies utilized to define the size and shape of a pixel) are substantially not attenuated. This generally implies that larger diameter lenses (e.g., about 10 to 100 millimeters) should be selected to mitigate attenuation of the spatial frequencies of interest.

Referring now to FIG. 5, a Modulation Transfer function 400 is illustrated in accordance with the present invention. On a Y-axis, modulation percentage from 0 to 100% is illustrated defining percentage of contrast between black and white. On an X-axis, Absolution Spatial Resolution is illustrated in terms of microns of separation. A line 410 illustrates that modulation percentage remains substantially constant at about 100% over varying degrees of spatial resolution. Thus, the Modulation Transfer Function is about 1 for the present invention up to about a limit imposed by the signal to noise sensitivity of the sensor. For illustrative purposes, a conventional optics design Modulation Transfer Function is illustrated by line 420 which may be an exponential curve with generally asymptotic limits characterized by generally decreasing spatial resolution with decreasing modulation percentage (contrast).

FIG. 6 illustrates a quantifiable Figure of Merit (FOM) for the present invention defined as dependent on two primary factors: Absolute Spatial Resolution (R_(A), in microns), depicted on the Y axis and the Field Of View (F, in microns) depicted on the X axis of a graph 500. A reasonable FOM called “Spatial Field Number” (S), can be expressed as the ratio of these two previous quantities, with higher values of S being desirable for imaging as follows: S=F/R _(A)

A line 510 illustrates that the FOM remains substantially constant across the field of view and over different values of absolute spatial resolution which is an enhancement over conventional systems.

FIGS. 7, 8, 14, 15, 16, and 20 illustrate methodologies to facilitate imaging performance in accordance with the present invention. While, for purposes of simplicity of explanation, the methodologies may be shown and described as a series of acts, it is to be understood and appreciated that the present invention is not limited by the order of acts, as some acts may, in accordance with the present invention, occur in different orders and/or concurrently with other acts from that shown and described herein. For example, those skilled in the art will understand and appreciate that a methodology could alternatively be represented as a series of interrelated states or events, such as in a state diagram. Moreover, not all illustrated acts may be required to implement a methodology in accordance with the present invention.

Turning now to FIG. 7 and proceeding to 610, lenses are selected having diffraction-limited characteristics at about the same size of a pixel in order to provide unit-mapping and optimization of the k-space design. At 614, lens characteristics are also selected to mitigate reduction of spatial frequencies within k-space. As described above, this generally implies that larger diameter optics are selected in order to mitigate attenuation of desired k-space frequencies of interest. At 618, a lens configuration is selected such that pixels, having a pitch “P”, at the image plane defined by the position of a sensor are scaled according to the pitch to an object field of view at about the size of a diffraction-limited spot (e.g., unit-mapped) within the object field of view. At 622, an image is generated by outputting data from a sensor for real-time monitoring and/or storing the data in memory for direct display to a computer display and/or subsequent local or remote image processing and/or analysis within the memory.

FIG. 8 illustrates a methodology that can be employed to design an optical/imaging system in accordance with an aspect of the present invention. The methodology begins at 700 in which a suitable sensor array is chosen for the system. The sensor array includes a matrix of receptor pixels having a known pitch size, usually defined by the manufacturer. The sensor can be substantially any shape (e.g., rectangular, circular, square, triangular, and so forth). By way of illustration, assume that a sensor of 640×480 pixels having a pitch size of 10 μm is chosen. It is to be understood and appreciated that an optical system can be designed for any type and/or size of sensor array in accordance with an aspect of the present invention.

Next at 710, an image resolution is defined. The image resolution corresponds to the smallest desired resolvable spot size at the image plane. The image resolution can be defined based on the application(s) for which the optical system is being designed, such as any resolution that is greater than or equal to a smallest diffraction limited size. Thus, it is to be appreciated that resolution becomes a selectable design parameter that can be tailored to provide desired image resolution for virtually any type of application. In contrast, most conventional systems tend to limit resolution according to Rayleigh diffraction, which provides that intrinsic spatial resolution of the lenses cannot exceed limits of diffraction for a given wavelength.

After selecting a desired resolution (710), a suitable amount of magnification is determined at 720 to achieve such resolution. For example, the magnification is functionally related to the pixel pitch of the sensor array and the smallest resolvable spot size. The magnification (M) can be expressed as follows:

$\begin{matrix} {M = \frac{x}{y}} & {{Eq}.\mspace{14mu} 1} \end{matrix}$

-   -   wherein:         -   x is the pixel pitch of the sensor array; and         -   y is the desired image resolution (minimum spot size).

So, for the above example where the pixel pitch is 10 μm and assuming a desired image resolution of 1 μm, Eq. 1 provides an optical system of power ten. That is, the lens system is configured to back-project each 10 μm pixel to the object plane and reduce respective pixels to the resolvable spot size of 1 micron.

The methodology of FIG. 8 also includes a determination of a Numerical Aperture at 730. The Numerical Aperture (NA) is determined according to well-established diffraction rules that relate NA of the objective lens to the minimum resolvable spot size determined at 710 for the optical system. By way of example, the calculation of NA can be based on the following equation:

$\begin{matrix} {{NA} = \frac{0.5 \times \lambda}{y}} & {{Eq}.\mspace{14mu} 2} \end{matrix}$

-   -   where:         -   λ is the wavelength of light being used in the optical             system; and         -   γ is the minimum spot size (e.g., determined at 710).

Continuing with the example in which the optical system has a resolved spot size of γ=1 micron, and assuming a wavelength of about 500 nm (e.g., green light), a NA=0.25 satisfies Eq. 2. It is noted that relatively inexpensive commercially available objectives of power 10 provide numerical apertures of 0.25.

It is to be understood and appreciated that the relationship between NA, wavelength and resolution represented by Eq. 2 can be expressed in different ways according to various factors that account for the behavior of objectives and condensers. Thus, the determination at 730, in accordance with an aspect of the present invention, is not limited to any particular equation but instead simply obeys known general physical laws in which NA is functionally related to the wavelength and resolution. After the lens parameters have been designed according to the selected sensor (700), the corresponding optical components can be arranged to provide an optical system (740) in accordance with an aspect of the present invention.

Assume, for purposes of illustration, that the example optical system created according to the methodology of FIG. 8 is to be employed for microscopic-digital imaging. By way of comparison, in classical microscopy, in order to image and resolve structures of a size approaching 1 micron (and below), magnifications of many hundreds usually are required. The basic reason for this is that such optics conventionally have been designed for the situation when the sensor of choice is the human eye. In contrast, the methodology of FIG. 8 designs the optical system in view of the sensor, which affords significant performance increases at reduced cost.

In the k-space design methodology, according to an aspect of the present invention, the optical system is designed around a discrete sensor that has known fixed dimensions. As a result, the methodology can provide a far more straight-forward, robust, and inexpensive optical system design approach to “back-project” the sensor size onto the object plane and calculate a magnification factor. A second part of the methodology facilitates that the optics that provide the magnification have a sufficient NA to optically resolve a spot of similar dimensions as the back-projected pixel. Advantageously, an optical system designed in accordance with an aspect of the present invention can utilize custom and/or off-the-shelf components. Thus, for this example, inexpensive optics can be employed in accordance with an aspect of the present invention to obtain suitable results, but well-corrected microscope optics are relatively inexpensive. If custom-designed optics are utilized, in accordance with an aspect of the present invention, then the range of permissible magnifications and numerical apertures becomes substantial, and some performance gains can be realized over the use of off-the-shelf optical components.

In view of the concepts described above in relation to FIGS. 1-8, a plurality of related imaging applications can be enabled and enhanced by the present invention. For example, these applications can include but are not limited to imaging, control, inspection, microscopy and/or other automated analysis such as:

(1) Bio-medical analysis (e.g., cell colony counting, histology, frozen sections, cellular cytology, Meachanical, Laser or radiation-based, and other Micro-dissection, Haematology, pathology, oncology, fluorescence, interference, phase and many other clinical microscopy applications);

(2) Particle Sizing Applications (e.g., Pharmaceutical manufacturers, paint manufacturers, cosmetics manufacturers, food process engineering, and others);

(3) Air quality monitoring and airborne particulate measurement (e.g., clean room certification, environmental certification, and so forth);

(4) Optical defect analysis, and other requirements for high resolution microscopic inspection of both transmissive and opaque materials (as in metallurgy, automated semiconductor inspection and analysis, automated vision systems, 3-D imaging and so forth); and

(5) Imaging technologies such as cameras, copiers, FAX machines and medical systems as well as other technologies/applications which are described in more detail below.

FIGS. 9-16 illustrate possible example systems that can be constructed employing the concepts previously described above in relation to FIGS. 1-8. It is to be appreciated that the pixel-mapping components and concepts can be applied to two-dimensional imaging systems and can also be applied to multi-dimensional system as well. For instance, more than one image can be taken using the subject imaging system, wherein respective images may be combined with each other to form highly resolved three-dimensional images using image reconstruction techniques.

FIG. 9 depicts an example packaging concept and system 900 for an imaging system adapted in accordance with the present invention. In this aspect, the system 900 includes imaging components such as a sensors, optics, and adjustments that provide imaging data to an associated computer (not shown) through substantially any desired coupling technique such as a Firewire, USB port, parallel port, infrared, and so forth. It is to be appreciated however, that a computer system (or portions thereof, e.g., memory components) could be provided within the system 900.

The system 900 can include such aspects as a k-space access panel at 910, various adjustment devices 920 and 930 for adjusting or positioning lenses and/or stages for viewing desired objects, and one or more access spaces 934 to insert an object sample. These adjustments, as well as sample ingress, egress, and handling, can be automated such as via servo controls, manual controls, or combinations of manual and automatic controls. Other features of the system 900 include Koehler iris controls 940, a projection/condensor access panel 944, and a transmissive illumination module 950 having an associated transmission illumination iris control 954. Other controls include an objective turret dial control 960 and an EPI-illumination control 964 associated with an Epi-illumination module 970. An Epi-Illumination access space 980 can also be provided.

FIG. 10 depicts a system assembly layout 1000 for the system 900 illustrated in FIG. 9, wherein such system can be configured in a hand held or portable arrangement (e.g., 10 inches by 12 inches apparent footprint). At 1010, an LED solid-state illumination source having an associated holographic/diffractive optical element is provided. At 1020, a projection condenser module is provided. At 1030, an illumination module assembly is provided. At 1040, a Koehler/Abbe microscope condenser and stage assembly is provided, each of the which may have axially moveable components for object focus. At 1050, turret mounted objective lenses are provided that can be axially moveable and lockable for object field of view focus. It is to be appreciated that such multiple objective configurations may include as many or few lenses as is practicable or desirable in any chosen design configuration. Also, rather than a turret, a linear slide configuration of lenses can be provided.

At 1060, a k-space access section is provided. At 1070, an optical path for filters and/or other optical components is provided. At 1078, an Epi-illumination assembly is provided having an associated holographic/diffractive optical element. It is noted that any of the light sources described herein can be adapted or changed for various different wavelengths. Also, different types of sources can be provided. For example, in certain low power applications, a conventional LED (having differing wavelengths) can be employed, whereas for other applications, a light source such as a Luxeon star can be employed. At 1080 a sensor detector module and access entry is provided. At 1084, a detector connector for sending image data to a computer is provided. At 1090, an exemplary battery/power module is provided and an AC or other power input can be provided at 1094.

FIG. 11 illustrates an optical train assembly 1100 in accordance with an aspect of the present invention. The assembly 1100 includes one or more of the following: an illumination source 1110, a holographic/diffractive optical element 1114, a condenser projection lens 1120 (generally aspheric), an iris diaphragm or aperture 1124, a field lens 1130, a Kohler or Abbe microscope condenser 1034, a moveable stage assembly 1140, a sample 1144 (e.g., transparent or opaque sample or slide), turret mounted microscope objectives 1150 (axially moveable and lockable for object Field of View focus), a beam splitter 1154, a telan or tube or field lens 1160, a detector system 1164 (CMOS, CCD, and so forth), an EPI illumination assembly 1168 having a projection lens 1170, an iris diaphragm/aperture 1174, a holographic/diffractive optical element 1180, and an illumination source 1184 (wavelength selectable devices).

FIG. 12 illustrates an alternative portable imaging and microscope device 1200 in accordance with an aspect of the present invention. In this aspect, a digital camera 1210 is adapted with a mapping lens 1220 (or lens assembly) to provide a hand held microscopic imaging device. The mapping lens 1220 provides projected pixel mapping or correlation between the camera sensor and a diffraction-limited spot defined by the lens. It is noted that in one example of a medical imager, by using numbers (below), approximately 1.75×1.32 millimeters of object can be imaged by the camera 1210—yielding approximately 25 pixels per red cell, and 100-500 pixels per white cell, at a resolution of 1 micron, for example. A haematology analysis can proceed with 1,000 cells (total), thus a single image will be capable of holding sufficient information for a full cell count. In an example design the following may apply:

1. select a desired resolution, e.g., 1 micron.

2. calculate that the objective lens would need an NA of approximately 0.3 based on example resolution of 1 micron.

3. calculate that the magnification required to get from 1 micron of resolution to 5.4 microns of pixel-quadrad pitch is approximately 5×

4. construct a k-space-transfer microscope with a 5×NA=0.3 objective lens

5. employ a digital camera (e.g., Sony DSC-F828), remove the lens sold with camera, and mate the camera to the k-space microscope described in 4.

In general, “desired” is what a CCD sensor (or other type) is capable of, wherein “3-filter” is what current CCDs perform (usually RGGB quadrads of pixels) and “4-filter” such as Sony performs (RGBC quadrad). Other non-rectangular geometries can also be employed, such as hexagonal or pentagonal, whereby more filters can be adapted on the extra pixels to further fill-in the colors currently missed by a 3-filter arrangement.

FIGS. 13-16 describe another exemplary portable system in accordance with the present invention. In general, in nearly all cases whereby a digital sensor is attached to an imaging system capable of high effective magnification, the resulting system is non-portable due to constraints of size, required power, and support infrastructure. One of the main considerations is that conventional systems are designed for human use, and do not take advantage of the inherent possibilities of a discrete sensor approach.

When an imaging system is designed to tale full advantage of the properties of a discrete sensor array, many of the design parameters that have to be considered for a conventional system can be discarded, leading to a greatly simplified system which exhibits a similar (or better) effective magnification, similar (or better) resolution, and much lower light requirements.

As an example of a reduced-size system, the following describes a fully-integrated haematology system (or other application) which has direct relevance to emerging (third-world) countries where a simple, fast blood analysis (e.g., HIV, sickle-cell anaemia) would be of great value.

Some considerations are that the system should be capable of being powered from a variety of sources (battery, line voltage, solar cell), should have a minimum of moving parts, and should have robust software (i.e., embedded firmware). In addition, the system cost should be minimal. Also, the system should be capable of performing all commonly utilized tests that involve samples as presented to a microscope on a slide substrate.

The following describes some possible considerations:

-   -   sensor considerations:     -   the sensor should be heavily integrated and not require complex         support circuitry     -   the sensor should require very little power     -   the sensor should be sensitive to low levels of light     -   the sensor should have a wide dynamic range     -   the sensor should have a large number of active sites (pixels)         but not be so large as to require excessive data transfer times         (i.e., 1k×1k array)     -   optical considerations:     -   the system should conform to k-space design parameters     -   the system should have as wide a field of view as practical     -   the system should be as near to focus-free as practical     -   the system should have a large depth of field     -   the system should use simple optical components     -   lighting considerations:     -   should have low power requirements     -   should require minimal user adjustment     -   should have extended life     -   mechanical considerations     -   the system should be very robust to allow for field-usage     -   the system should allow easy field-servicing     -   the system should be as modular as possible     -   the system should be light to allow for portability     -   digital considerations     -   computing power is not a necessity, so a moderately         low-performance computing platform will suffice     -   very low electrical power consumption     -   common computing functions should be integrated onto the main         computing platform     -   outputs for LCD and CRT should be provided for flexibility     -   provision for external storage for any presently extant or         future strorage media should be made, with interfaces for floppy         disk, memory stick, USB memory adapter, printer, CDROM, DVDROM,         and/or hard disk     -   basic computing functions, such as the operating system and         application software should be embedded in non-volatile storage         such as ROM or flash memory, leading to diskless operation     -   the OS and application software should be robust and capable of         extension either on-site by the user, or remotely by e.g.,         dialup or wireless internet connection.

One example implementation of the above system:

-   -   sensor:     -   a CMOS array with the above-described characteristics, and is         available in sizes from 640×480 to 1280×1024 with pixels of         approximately 5 microns.     -   typical power requirements are in the low 10's of milliwatts.     -   optics as depicted in the optical configuration 1300 of FIG. 13:     -   for a haematology analysis system, a base resolution of one         micron per pixel is quite sufficient to resolve and identify red         cells (5 um) and white cells (25 um).     -   referring to the proposed CMOS sensor, this leads to an optical         magnification of 5× requirement to map a single pixel onto the         object plane with a resolution of 1 um.     -   for a magnification of 5×, and a projected pixel-pitch of 1 um,         the required Numerical Aperture of the imaging lens to provide a         diffraction-limited 1 um spot is 0.25.     -   for such modest magnification requirements, the optical design         can be met using a simple Gauss-pair of achromats 1310 and 1320.         The optimal design would use     -   a sensor lens of focus f=150 mm, diameter d=25 mm     -   an imaging lens of f=30 mm, d=25 mm (giving an NA of slightly         greater than 0.25)     -   referring to an example 1280×1024 pixel sensor and the above         optical prescription, an imaging system is provided capable of 1         um resolution with a field of view of 1.2 mm×1 mm, and depth of         focus (field) approaching 10 microns.

FIG. 14 illustrates a lighting system 1400 having possible parameters as follows:

-   -   white LEDs should be used with consequently low power         requirements (<50 mW) and long operating life (50,000+hours)     -   light homogenisation via holographic diffusers should be used         (leading to a virtual point-source)     -   Kohler sub-stage (transmissive) lighting should be provided     -   option should be made for white-light or UV epi-illumination if         required.     -   optomechanics     -   components should be standard sizes (e.g. 25 mm/1 inch diameter)     -   components should be corrosion-resistant (due to the         commonly-met chemical environment in haematology)     -   all components should be easily assembled in the form of modules     -   e.g., components from Thorlabs, Linos and similar

FIG. 15 illustrates an example processing system 1500 having possible configurations of:

-   -   the processor of can be an ARM range (Advanced RISC Machines or         other type), which are widely accepted as having the best         performance to power ratio. Additionally, many of the ARM         variants are available as “system on chip” designs, where a CPU,         FPU, IO and Video subsystems are fully integrated into a         single-chip package (e.g., ARM 7500 FE, StrongARM 1110)     -   the operating system can be a RISCOS (or other type), which is a         ROM-based OS that has both high- and low-level abstractions, is         very robust, and has been deployed since 1987. It also has a         very simple and intuitive graphical user interface. Code         density, due to the RISC techniques employed, is very good, and         major applications generally only use 100's of kilobytes.     -   typically, complete computing systems can be obtained that make         use of RISCOS and the ARM processors in the form of single-board         computers. Power requirements very rarely exceed 5-10 Watts.         On-board storage is typically supplied in the form of flash         memory (16-64 megabytes). Common sizes for the computer boards         are 100 mm×150 mm, and this has lead to the availability of         low-power LCD displays with integrated computer boards (e.g.,         Explan SOLO, Castle SLYM)     -   for a completely integrated haematology solution (or other         application), direct interfacing of the sensor array into the         main memory space of the host computer avoids complications and         expense consequent with standard interfaces (e.g., USB,         IEEE-1394), and also allows simple control of the sensor         functions. Some sophistication can be achieved by using         double-buffered memory (e.g., VRAM) to act as an arbitrator         between the sensor and the host CPU.     -   for the above-described system, power requirements generally         fall within a 10 watt power budget, and can be met by battery,         line, or solar-cell supplies.         Software:     -   should be implemented with a simple graphical user interface     -   should be capable of identifying red cells, white cells, and         sickle-cells (deformed erithrocytes)     -   should be capable of performing simple counts and blood         differentials     -   should present results visually (displayed image) and textually         (data list)     -   should offer off-line storage on removable media (e.g., floppy         disk, memory stick) or as a simple printout     -   should be capable of being expanded via a modular interface to         allow for more sophisticated analyses     -   should be capable of being distributed in varying formats (e.g.,         on a storage medium, as a data stream via remote connection, or         as a ROM-module).     -   should be well-documented and open-source, if possible, to allow         for onsite modifications

FIG. 16 illustrates a system 1600 that provides the following features:

-   -   fully-integrated and portable     -   a baseplate 1610 holding an optics/sensor module, a lighting         module, and a sample presentation module     -   single-board computer coupled to baseplate 1610, carrying         display (LCD)     -   expansion unit carrying printer/floppy disk.

FIG. 17 illustrates an alternative imaging design in accordance with an aspect of the present invention. In this aspect, a highly modular and portable system 1700 is illustrated from a top view. The system 1700 includes a handheld computer 1710 having a digital camera integrated or associated therewith. Such computers 1710 can include wired ports such as USB ports or wireless ports such as Bluetooth, for example, for transferring electronic images between locations in accordance with the present invention. Although, a Hewlett-Packard iPAQ computer is illustrated at 1710, it is to be appreciated that a plurality of vendors supply such devices such as Sony, Casio, Palm, Dell, Viewsonic, Toshiba, Sharp, Phillips, JVC, and so forth, for example.

Other components illustrated on the system 1700 for generating microscopic images can include one or more mirrors at 1720 and 1730, a matching lens at 1740, a resolution lens at 1750, a stage component at 1760 where the object plane resides, an illumination lens at 1770, a light source mount at 1780 (e.g., LED mount), and a power supply 1790 (e.g., battery, regulated AC supply). In this example, the lens 1740 and 1750 map the characteristics of a pixel associated with the camera that has been integrated with the computer 1710 in accordance with the diffraction limits of the lens as described above. For example, if a 2.7 micron pixel was the pixel pitch associated with the camera, and a 0.65 Numerical Aperture resolution lens 1750 were selected providing about 384 nanometer resolution for white light, then the overall magnification of the matching lens 1740 and the resolution lens 1750 would be selected to be about 7.03× (× refers to times magnified). Thus, 7.03× in this example maps 384 nanometer resolution with 2.7 micron pixels (2.7/0.384 is approximately 7.03125). Although components are laid out in a planar or two-dimensional arrangement in the system 1700, it is to be appreciated that the components can be arranged in two and/or three-dimensional arrangement, wherein optics, computers, components, and/or sensors are configured circumferentially or other maimer with respect to one another in order to minimize planar real estate of the overall configuration. Other views of the system 1700 are illustrated at 1792 through 1798.

It is noted that many manufacturers and other institutions teach that to conform to the Nyquist criterion that at least two and preferably three pixels should be provided for each diffraction-limited spot or parameter defined by the Numerical Aperture of the lens. This is substantially in contravention to the present invention that maps less than two pixels per spot (e.g., the size of one pixel matched via the optics to the size of the diffraction-limited spot). Thus, the camera described above generally includes a sensor having one or more pixels, whereby the pixels have a pixel pitch or resolution parameter, and the pixel pitch is correlated to the optical components. Thus, in accordance with the present invention, any mapping that is less than two pixels per spot is within the scope of the present invention, wherein it is noted that fractional mappings are possible (e.g., 1.999 pixels per spot, 1.5 pixels per spot, 1.0 pixels per spot, 0.9 pixels per spot, 0.7 pixels per spot).

In one aspect of the invention, the pixel size is one of a pixel pitch (for any pixels), pixel length (for square pixels), and pixel width (for rectangular pixels), that is about 0.1 microns or more and about 20 microns or less. In another aspect of the invention, the pixel size is one of a pixel pitch (for any pixels), pixel length (for square pixels), and pixel width (for rectangular pixels), that is about 0.25 microns or more and about 15 microns or less. In yet another aspect of the invention, the pixel size is one of a pixel pitch (for any pixels), pixel length (for square or rectangular pixels), and pixel width (for square or rectangular pixels), that is about 0.5 microns or more and about 10 microns or less. In still yet another aspect of the invention, the pixel size is one of a pixel pitch (for any pixels), pixel length (for square or rectangular pixels), and pixel width (for square or rectangular pixels), that is about 4 microns or more and about 9 microns or less.

In one aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is between 1:2 and 2:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.9 to about 1.9:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.7 to about 1.7:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.5 to about 1.5:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.4 to about 1.4:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.3 to about 1.3:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.2 to about 1.2:1. In another aspect of the invention, the ratio of the projected pixel size to the diffraction spot size, both in the object plane and determined by pitch, length, width, or diameter, is from about 1:1.1 to about 1.1:1.

With respect to another consideration, the pixel size matching to the diffraction-limited spot results in a tuning of the lenses (or optical components) and pixels so that desired “spatial” frequencies of interest are received by respective pixels. Without such matching (as in conventional microscopy systems) adjoining pixels may individually receive only a subset of “spatial frequencies” of interest thereby not taking full advantage of capabilities of respective pixels. Moreover, since the pixels are unaware (e.g., not correlated to) of what subset of the spatial frequencies they are respectively receiving, indeterminacy results when trying to reconstruct the superset of spatial frequencies associated with a diffraction-limited spot as received by the set of adjoining pixels. On the other hand, by size matching individual pixels to the diffraction-limited spot associated with a given set of lenses as in the present invention, such indeterminacy is substantially mitigated since the superset of spatial frequencies of interest are substantially received by individual pixels. Because there are gaps between pixels in an array and thousands/millions of pixels being exposed to an image projection, there may be some level of indeterminacy; however, the subject invention significantly mitigates such indeterminacy as compared to conventional systems that fail to contemplate let alone address the advantages associated with the tuning that results by size mapping of pixels to the diffraction-limited spot as in the subject invention. In view of the pixel-mapping concepts described above, the following concepts can also be considered:

1. Substantially ensure that all of the information contained in a single diffraction-limited spot is captured by the pixel (sensor).

2. Provide a significantly enhanced signal-to-noise ratio (SNR) per pixel due to the information in the spot being captured by the pixel. Thus, if two pixels per diffraction-limited spot were provided for example in a conventional system, the intensity per pixel is reduced to about a quarter of the about 1:1 matching case of the present invention.

3. There is no guarantee that a diffraction-limited spot (DLS) has a uniform distribution of energy, thus in the multiple-pixel case per spot as in conventional systems, one has substantially no concept of which pixel is sampling which bit of the DLS.

4. Generally, references to the “point spread response” (PSR) refer to the instrument capturing the image, and not the image itself. Thus, a DLS can be modeled as a convolute of the PSR and the fourier transform of the blob or object specimen being imaged.

To illustrate the above concepts, the following tables are provided to highlight some example differences between the present invention and conventional microscopic systems.

Microscope Comparison Conventional Design (Optimized for human eye) Conventional Design Examples: Total (with Depth of Working 10x eyepiece) Resolution NA Field Distance Objective Magnification 2,500 nm   0.10  100 um 22.0 mm  4x  40x 1,000 nm   0.25   16 um 10.5 mm 10x 100x 625 nm 0.40 6.25 um 1.20 mm 20x 200x 384 nm 0.65 2.40 um 0.56 mm 40x 400x 200 nm 1.25 0.64 um 0.15 mm (oil) (oil) 100x  1000x 

By comparison to the above table, if a 2.7 micron pixel were employed, for example, the present invention can provide 2500 nm resolution with about 1.1× magnification, 1000 nm resolution with about 2.7× magnification, 625 nm resolution with about 4.32× magnification, 384 nm resolution with about 7.03× magnification, and 200 nm resolution with about 13.5× magnification.

Performance Comparison between Conventional Systems and Present Invention Present invention lens design diameter about 25 mm, for example. Optimum conventional resolution occurs at approximately 1000 × NA (See standard optics literature) Example Present Invention Optical Parameters Conventional Microscope Depth Magnification Required Resolution Resolution NA of Field Working Distance Magnification For resolution (10x eyepiece) Performance 2,500 nm 0.10  100 um 125 mm  1x 100x 1/100 1,000 nm 0.25   16 um 48 mm 3x 250x 1/80    625 nm 0.40 6.25 um 28 mm 4x 400x 1/100   384 nm 0.65 2.40 um 14 mm 7x 650x 1/93 

Thus, by observing the above tables, it is illustrated that resolution in the present invention can be achieved with about 100 times less magnification than conventional systems employ when viewed in terms of a 2.7 micron pixel. This facilitates such features as greatly improved working distances for example along with allowing high performance, low cost, compact, modular, and robust microscopy systems to be employed.

It is noted that many variants are possible in accordance with the present invention. For example, many cell phones are equipped with digital cameras and thus, the cell phone or similar instrument could be employed in place of or in addition to the computer 1710 described above. Consequently, if an image were captured by the cell phone, the image could be transferred to various locations by dialling a respective number and transferring the image or images to the location dialled (e.g., web site, remote server, another cell phone or computer). In another example, the light source 1780 described above can be varied according to differing situations. For example, the light source can include a laser light source or other type that is tuned or adjusted (e.g., manually and/or automatically) to different frequencies in order to fine-tune the characteristics of the diffraction-limited spot in order to provide desired mapping to the pixel in accordance with the present invention. Alternatively, if a lens or sensor were changed and having differing characteristics, the light source can be adjusted accordingly to map the characteristics of the diffraction-limited spot to the characteristics of the projected pixel in the object field of view.

It is to be appreciated that substantially any system or components that performs pixel-mapping or resolution-mapping in an approximately one-to-one manner is considered within the scope of the present invention. In one example, although pixelated sensor arrays are generally employed, other type sensors can be mapped in accordance with the present invention. For example, a beam scanning type sensor (e.g., vidicon tube) that is scanned by a beam of light to reproduce an image captured thereon can be described by a beam spot having finite physical dimensions (e.g., beam diameter) that is moved across the sensor to detect images thereon. In this example, the optics can be adapted such that the dimensions of the beam spot are mapped to the dimensions of the beam diameter or spot in the object field of view as previously described.

FIG. 18 illustrates an excitation application 1800 in accordance with an aspect of the present invention that can be employed with the systems and processes previously described. A k-space system is adapted in accordance with the present invention having a light system that includes a light source at 1810, such as a Light Emitting Diode (LED), emitting light having a wavelength of about 250 to about 400 nm (e.g., ultraviolet light). The LED can be employed to provide for epi-illumination or trans-illumination as described herein (or other type). The use of such an LED (or other UV light source) also enables wave-guide illumination in which the LTV excitation wavelength is introduced onto a planar surface supporting the object under test at 1820, such that evanescent-wave coupling of the UV light can excite fluorophores within the object. For example, the UV light can be (but not limited to) provided at about a right angle to a substrate on which the object lies. At 1830, the LED (or other light source or combinations thereof) can emit light for a predetermined time period and/or be controlled in a strobe-like manner emitting pulses at a desired rate.

At 1840, excitation is applied to the object for the period determined at 1830. At 1850, automated and/or manual analysis is performed on the object during (and/or thereabout) the excitation period. It is noted that the excitation application 1800 described herein can apply to various processes. In one aspect, this includes a process wherein a high-energy photon (short wavelength) is absorbed and subsequently re-emitted as a lower-energy photon (longer wavelength). The time interval between absorption and emission generally determines whether the process is one of fluorescence or phosphorescence—which can also be defined as a “down-conversion” process.

By way of illustration, the object which is sensitive to ultraviolet in that it absorbs/emits photons in response to excitation of UV light from the light source. Fluorescence (or phosphorescence) is a condition of a material (organic or inorganic) in which the material undergoes a process wherein a high-energy photon (short wavelength) is absorbed and subsequently re-emitted as a lower-energy photon (longer wavelength). The time interval between absorption and emission generally determines whether the process is one of fluorescence or phosphorescence—which can also be defined as a “down-conversion” process. It can also continue to emit light while absorbing excitation light. Both Fluorescence and phosphorescence can be an inherent property of a material (e.g., auto-fluorescence) or it can be induced, such as by employing fluorochrome stains or dyes. The dye can have an affinity to a particular protein, chemical component, physical component, and/or other receptiveness so as to facilitate revealing or discovering different conditions associated with the object. In one particular example, fluorescence microscopy (or phosphorescence microscopy) and/or digital imaging provide a manner in which to study various materials that exhibit secondary fluorescence (or phosphorescence).

By way of further example, the UV LED (or other source) can produce intense flashes of UV radiation for a short time period, with an image being constructed by a sensor (sensor adapted to the excitation wavelength) a short time later (e.g., milliseconds to seconds). This mode can be employed to investigate the time decay characteristics of the fluorescent (or phosphorescent) components of the object (or sample) being tested. This may be important where two parts of the object (or different samples) may respond (e.g., fluoresce/phosphorescence substantially the same under continuous illumination, but may have differing emission decay characteristics.

As a result of using the UV light source, such as the LED, the light from the light source can cause at least a portion of the object under test to emit light, generally not in the ultraviolet wavelength. Because at least a portion of the object fluoresces, (or phosphoresces) pre- or post-fluorescence/phosphorescence images can be correlated relative to those obtained during fluorescence/phosphorescence of the object to ascertain different characteristics of the object. In contrast, most conventional systems are configured to irradiate a specimen and then to separate the weaker re-radiating fluorescent light from the brighter excitation light, typically through filters. In order to enable detectable fluorescence, such conventional systems usually require powerful light sources. For example, the light sources can be mercury or xenon arc (burner) lamps, which produce high-intensity illumination powerful enough to image fluorescence specimens. In addition to running hot (e.g., typically 100-250 Watt lamps), these types of light sources typically have short operating lives (e.g., 10-100 hours). In addition, a power supply for such conventional light sources often includes a timer to help track the number of use hours, as arc lamps tend to become inefficient and degrade with decreasing or varying illumination output with use. The lamps are also more likely to shatter, if utilized beyond their rated lifetime. Moreover, conventional light sources such as Xenon and mercury arc lamps (burners) generally do not provide even intensity across the desired emission spectrum from ultraviolet to infrared, as much of the intensity of the mercury burner, for example, is expended in wavelengths across the near ultraviolet. This often requires precision filtering to remove undesired light wavelengths. Accordingly, it will be appreciated that using a UV LED, in accordance with an aspect of the present invention, provides a substantially even intensity at a desired LV wavelength to mitigate power consumption and heat generated through its use. Additionally, the replacement cost of a LED light source is significantly less than conventional lamps.

In accordance with the foregoing discussion it will be appreciated that the excitation source may also be any other light source so desired for irradiation of an object through the k-space region as described above. This could be, by way of example, an appropriate laser source. Such a laser source could be chosen to be applicable to applications of Multi-photon Fluorescence Microscopy.

By way of further example, it will be appreciated that referring again to FIG. 18 an excitation application is illustrated at 1800 in accordance with an aspect of the present invention that can be employed with the systems and processes previously described. A k-space system is adapted in accordance with the present invention having a light system that includes a Laser light source, such as (but not limited to) Ti:Sapphire Mode-Locked Lasers, and/or Nd:YLF Mode-Locked Pulsed Lasers. Such Lasers can be employed to provide for epi-illumination or trans-illumination as described herein (or other type). The use of such a Laser (or any other) also enables wave-guide illumination in which the excitation wavelength is introduced onto a planar surface supporting the object under test, such that evanescent-wave coupling of the Laser light can excite fluorophores within the object in accordance with the desired parameters of Multi-photon Fluorescence Microscopy. For example, the Laser light can be (but not limited to) provided at about a right angle to a substrate on which the object lies. The Laser source (or combinations thereof) can emit light for a predetermined time period and/or be controlled in a strobe-like manner emitting pulses at a desired rate. Automated and/or manual analysis can be performed on the object during (and/or thereabout) the excitation period. It is noted that the excitation application described herein can apply to various processes. In one aspect, this includes a process wherein Multi-photon Fluorescence Microscopy is the desired result. The present invention may be employed in any configuration desired (e.g., upright or inverted, or any other disposition such that the fundamental advantage of the optical design is employable.)

Since excitation in multi-photon microscopy occurs at the focal point of a diffraction-limited microscope it provides the ability to “optically section” thick biological specimens in order to obtain three-dimensional resolution. These “optical sections” are acquired, typically, by raster scanning the specimen in the x-y plane, and “building” a full “three-dimensional image” which is composed by scanning the specimen at sequential z positions in series. Multi-photon fluorescence is useful, for example, for probing selected regions beneath the specimen surface. This is because the position of the focal point can be accurately determined and controlled.

The lasers commonly employed in optical microscopy are high-intensity monochromatic light sources, which are useful as tools for a variety of techniques including optical trapping, lifetime imaging studies, photo bleaching recovery, and total internal reflection fluorescence. In addition, lasers are also the most common light source for scanning confocal fluorescence microscopy, and have been utilized, although less frequently, in conventional wide field fluorescence investigations.

It will be appreciated that an aspect of the present invention could incorporate a suitable exciting laser source. It is noted that typical lasers employed for Multi-photon fluorescence currently include the Ti:sapphire pulsed laser and Nd:YLF (neodymium: yttrium lithium fluoride) laser (as well as other available laser sources.) The first is self mode-locked in operation and produces laser light over a broad range of near-infrared wavelengths with variable pulse widths and generally adjustable speed. The exciting laser is joined to the present invention through a suitable port. This could be accomplished employing fiber coupling with an optical wave-guide or direct coupling with relay mirrors placed by design to direct the laser energy through the k-space region to the object.

A typical multi-photon fluorescence microscope incorporates a detector system (e.g., a filtered photo multiplier or photodiode or other such detector to the laser wavelength) disposed in concert with an x-y raster scanning device which can rapidly deflect the focused laser beam across the objective field. Digital images collected by the microscope are processed and analyzed by a computer and associated software processing to assemble three-dimensional reconstructions from the “optical sections.” These images display typical of the image sensor-visual microscope combination. Modern Multi-photon fluorescence microscopy has become a preferred technique for imaging living cells and tissues with three-dimensionally resolved fluorescence imaging since two-photon excitation, which occurs at the focal point of the microscope, minimizes photo bleaching and photo damage (the ultimate limiting factors in imaging live cells.) This in itself allows investigations on thick living tissue specimens that would not otherwise be possible with conventional imaging techniques.

The mechanisms that enable sophisticated multi-photon fluorescence microscopy result from two-photon and three-photon excitation, for example. These occur when two or three photons are absorbed by fluorophores in a quantitized event. Photons can, in this way be absorbed at high enough photon by combining their energies to force an electronic transition of a fluorosphore to the excited state.

FIGS. 19-20 illustrate beam-scanning technologies that can be applied to increase excitation yields in accordance with an aspect of the present invention. With respect to FIG. 19, an epi-fluorescence system 1900 is illustrated that includes a resolution lens 1910 and matching lens 1920 that are adapted to provide diffraction limited mapping of pixels from a camera/sensor 1930 to about the size of diffraction spots associated with the resolution lens 1910 as previously described. A fold mirror 1940 can be provided to direct energy from the matching lens 1920 to the camera/sensor 1930. A beam scanner 1950 is provided to increase or focus the amount of energy from an excitation source 1960 that is received by the camera/sensor 1930. A beam expander 1970 can also be included between the beam scanner 1950 and the excitation source 1960, wherein a beam splitter 1980 is employed to enable object illumination and to direct energy to the camera/sensor 1930.

In this aspect of the present invention, energy from the excitation source 1960 is applied in a beam diameter or dimension that is about the size of a diffraction-limited spot. In this manner, energy from the source 1960 is intensified at the pixel level and thus greatly increases the amount of energy received by the sensor 1930. Since a fully spatially quantised and resolved system 1900 is being employed, there are advantages to providing a fluorescent excitation where the excitation energy substantially matches the optical spatial quantisation. In general, the following considerations can be applied:

1. Maintain current preservation of spatial information.

2. There is substantially no “spillage” of excitation photons onto nearby pixels, thereby greatly reducing the amount of pixel fluorescent cross talk.

3. Rather than exciting the entire field of view, a single pixel (or subset) is concentrated on, thereby providing a fluorescent yield enhancement about equal to the number of pixels in the field of view (FOV). For a modest sensor, this can amount to a million-fold increase in yield, for example.

4. For a scanning excitation source, the system 1900 provides the ability to selectively scan the FOV and thereby isolate fluorescent structures of interest.

5. The excitation dosage can be altered by modulating the excitation source scan frequency, or by modulating the intensity of the excitation source, for example.

It is noted that the imaging path is generally unaffected, with the exception that the epi-illumination beam splitter 1980 can be a dichroic mirror highly reflective at the excitation wavelength (usually in the near-UV or deep-blue range). Also, it is desirable that the resolution lens 1910 (comparable to a conventional objective lens) should be transparent at the excitation wavelengths, if those wavelengths fall outside of the usual visible pass-band, for example.

It is further noted that yield can be increased in other aspects. For example, the excitation source 1960 (e.g., LED) can be pulsed via high current and short duration pulses to provide intense periods of brightness yet protect the source from excess power dissipation. This can be achieved with custom circuits that generate the pulses or via commercially available LED driver chips (e.g., Analogic Technologies 500 mA charge pump). These chips are high current charge pumps that can generate a large current through an LED in a very short time to provide a pseudo-flash. Thus, the system 1900 can synchronize the high-power strobing of an LED with a scan step frequency of a fluorescence microscope or system 1900, and significantly pump up the fluorescence yield. Typically the chips provide a 500 mA pulse to the LEDs, whereas an LED is typically run at 20 mA continuous, for example.

It is also noted that beam scanning can occur at varying degrees of offset, wherein images taken at different scanning offsets can be combined via software to mitigate positional uncertainty for the diffraction-limited spots. In one example, two flying-spot images could be captured for a given specimen. The first image would be with the projected illumination lining up with the projected pixels. The second image would be taken with the projected illumination lining up with the spaces between the pixels. These images can be referred to as full- and half-step images. The two images would then be digitally processed to form a resultant final image to reduce positional uncertainty.

FIG. 20 illustrates example scanning technologies that can be employed with the system depicted in FIG. 19. It is to be appreciated that any scanning system that promotes focusing of energy on a single pixel or a small subset of pixels is considered to be within the scope of the present invention. At 2010, orthogonal mirrors driven via servos, galvanometers or other motors, can be arranged to steer an excitation source around the epi-illumination path described above with respect to FIG. 19. This type scanning includes possible advantages of low cost and good optical quality with possible disadvantages of relatively low speed and a folded optical path. At 2020, orthogonal optical wedges can be employed and arranged to rotate about the optical path, and to cause a refractive shift in the direction of the excitation beam. This type scanning can include possible advantages of an in-line optical path and moderate speed while possible disadvantages may include refractive distortions. At 2030, electro-optic modulator crystals can be employed for scanning. These can include possible advantages of being fast and in-line with the optical path with possible disadvantages that include expense, high voltages, and small path divergences.

FIG. 21 illustrates an example system for integrating or retrofitting pixel-mapping components in accordance with an aspect of the present invention. In this aspect, portions of a conventional microscopic system 2100 include an objective lens and stage at 2110 that is illuminated from a sub-stage lighting module 2120. Light or energy from the objective 2110 is directed through a telan lens and fold mirror at 2130 that is again magnified via an eyepiece 2140. The system 2100 includes what is referred to as infinity space 2150 which can enable modules to be inserted into the space to perform functions such as auto-focus, epi-illumination, fluorescence, phase encoding, filtering and so forth. In this aspect of the present invention, a camera (or sensor) 2160 is associated with a matching lens 2170 that maps a diffraction limited spot size of the objective 2110 to about the size of a pixel at the camera or sensor. A beam splitter 2180 is employed to direct or divert some energy from the infinity space 2150 to the matching lens 2170 and camera 2160.

In general, conventional microscope systems are designed so that there is an “infinity path” or space 2150 between the objective lens 2110 and the telan 2130/eyepiece 2140 lens assembly. This space 2150 is conventionally used for additions such as epi-illumination, wavelength filtering, and so forth. Addition of a digital camera to a conventional system is almost universally achieved by the addition of a lens system within the main optical path, with the lens power arranged so that the camera sensor “sees” the same field of view as the eyepiece 2140 (and therefore the observer). It is usual to ensure that the sensor has a large number of pixels, so that the field of view is finely divided. Unfortunately, this approach ensures that the camera sensor is not optimally matched to the diffraction-characteristics of the objective lens 2110, but more to the viewing capabilities of the eyepiece 2140. This leads to a marked drop in potential performance.

The present invention optimizes performance by matching pixel characteristics of the camera 2160 to that of the objective 2110 rather than to the eyepiece 2140. Thus, the camera 2160, matching lens 2170, and beam splitter 2180 cooperate as an add-on or modifier component to a conventional system's infinity space 2150 (or other space) that enable optimized digital images to be produced at desired resolutions specified by the objective 2110. It is to be appreciated that any sensor and/or lens that is added to (or modifies) a microscopic system (e.g., industrial, commercial, or medical) to facilitate pixel-scaling of sensor pixels to about the size of the diffraction-limited spot size is considered to be within the scope of the present invention. Also, it is noted that diffraction performance can be defined by different methods such as geometrically via the wavelength of light and the Numerical Aperture of the objective, via the Rayleigh criterion, via Airy disk description, or via other descriptions such as Sparrow's criterion. It is to be appreciated that any technique that maps pixel dimensions to about the size of the diffraction-limited performance of a lens is considered to be within the scope of the present invention. The following describes some example implementations for constructing pixel-mapping components in accordance with the present invention.

In general, light or energy diverted from the infinity path 2150 by the beam splitter 2180 is directed towards the matching lens 2170, and thereby allowed to fall onto pixels that comprise a sensor or camera 2160. The matching lens' power (focal length) should be designed to closely match the object-plane diffraction-limited spot size to the pixel dimensions, thereby achieving an optimized configuration at desired resolutions specified by the objective lens 2110. Given that conventional objective lenses have a range of powers and numerical apertures, it is convenient in one aspect, to select the matching lens to perform for a range of objectives. This would have the effect of causing a conventional microscope that is optimized for a range of magnifications, concurrently becoming optimized for a range of resolutions. As can be appreciated, the matching lens 2170 could be provided in a multiple lens configuration, wherein the lenses in the configuration are mechanically switched (in or out) to match the capabilities of differing objective lenses 2110 (e.g., turret of matching lenses adjusted when the objective lens 2110 is changed—turret could also be synchronized with objective lens turret).

Consider the following sensor examples:

1. State-of-the-art sensor with 2.7 micron (um) pixels

2. Current “good” sensor with 5.0 micron (um) pixels

3. Low-cost sensor with 7.5 micron (um) pixels

For three of the most commonly used objective lenses (can also be custom manufactured lenses), the following performance characteristics may apply:

Magnification NA Resolution  10x 0.25  1.0 um  20x 0.40 0.625 um  40x 0.65 0.384 um 100x (oil) 1.25 0.200 um

(It is noted that the “magnification” listed in the above chart is valid only for a telan/tube lens of focal length 150 mm).

From the above example lens and sensor characteristics, the information to create matching lens prescriptions is provided in the following examples:

Pixel size Resolution Magnification Lens focal length  2.7 um  1.0 um 2.7x 40.5 mm 0.625 um 4.3x 32.4 mm 0.384 um 7.0x 26.4 mm 0.200 um 13.5x 20.3 mm  5.0 um  1.0 um 5.0x 75.0 mm 0.625 um 8.0x 60.0 mm 0.384 um 13.0x 48.8 mm 0.200 um 25.0x 37.5 mm  7.5 um  1.0 um 7.5x 112.5 mm  0.625 um 12.0x 90.0 mm 0.384 um 19.5x 73.2 mm 0.200 um 37.5x 56.3 mm

The beam splitter 2180 can be any of the following examples:

1. a beam splitting cube (polarizing or non-polarizing) with symmetric (e.g., 50:50) or asymmetric (e.g., 70:30) splitting ratios

2. a plane beam splitter, antireflection-coated on one surface, and coated on the other surface to provide a suitable splitting ratio (symmetric or asymmetric)

3. a thin pellicle.

As can be appreciated, the above sensors and lenses were chosen for illustrative purposes. Thus, any sensor and/or lens combination that scales or maps diffraction limited performance of a lens to about the size of a pixel dimension (e.g., pitch) is considered to be within the scope of the present invention.

What has been described above are preferred aspects of the present invention. It is, of course, not possible to describe every conceivable combination of components or methodologies for purposes of describing the present invention, but one of ordinary skill in the art will recognize that many further combinations and permutations of the present invention are possible. Accordingly, the present invention is intended to embrace all such alterations, modifications and variations that fall within the spirit and scope of the appended claims. 

1. A system for generating a digital image, comprising: a sensor having a plurality of pixels to generate an image for the optical system; an object plane for positioning therein one or more items under microscopic examination; and optical media for imaging an object, wherein the optical media defines an image plane, to scale the pixels and to project virtually-reduced pixels in the image plane in accordance with at least one of the following criteria: (a) the individual virtually-reduced pixels are about a size of a diffraction-limited parameter associated with the optical media; (b) the individual virtually-reduced pixels are a size of at minimum 0.1% to at maximum about the same size as a diffraction-limited parameter associated with the optical media; or (c) a diffraction-limited parameter associated with the optical media is a size of at minimum 0.1% and at maximum about the same size of the individual virtually-reduced pixels; wherein the optical media is associated with the sensor; the optical media defines in the object plane one or more of a Blur-circle, an Airy disk, and a diffraction-limited spot and one or more of a Blur-circle, an Airy disk, and diffraction-limited spot is one or more of matched, unit-mapped, correlated with the pixels; and the optical media defines that a Modulation Transfer Function of the sensor can be matched to Modulation Transfer Function of the object plane.
 2. The system of claim 1, the sensor is associated with a digital camera.
 3. The system of claim 1, the optical media further comprising an infinity path to enable receiving the image at the sensor.
 4. The system of claim 3, further comprising a beam splitter to direct the image to the sensor.
 5. The system of claim 4, the beam splitter includes at least one of a beam splitting cube, a plane beam splitter, and a thin pellicle.
 6. The system of claim 3, the optical media is adapted to the infinity path to enable retrofitting of a digital imager into an existing system.
 7. The system of claim 3, the infinity path enables at least one optical module to be associated with the path.
 8. The system of claim 7, the optical module includes at least one of an auto focus module, an epi illumination module, a fluorescence module, a phase encoding module, and a filter module.
 9. The system of claim 1, the optical media is at least one of an industrial optical system, a commercial optical system, and a medical optical system.
 10. The system of claim 1, the diffraction-limited parameter is associated with at least one of a geometrical criterion defined by an energy wavelength and a Numerical Aperture, a Rayleigh criterion, an Airy disk criterion, and a Sparrow's criterion.
 11. The system of claim 1, wherein the optical media comprises an objective lens and a matching lens, wherein the matching lens has a focal length designed to approximate an object-plane diffraction-limited spot size with a pixel dimension.
 12. The system of claim 11, the objective lens comprising a magnification of 10×, 20×, 40×, or 100×.
 13. The system of claim 11, further comprising a set of matching lenses that are correlated to provide diffraction-limited mapping of pixels with a set of objective lenses.
 14. The system of claim 1, the pixels have pitch size of about 2 microns to about 10 microns.
 15. The system of claim 14, further comprising the pixels associated with a resolution lens having a numerical aperture from about 0.1 to about 1.3.
 16. The system of claim 14, further comprising the pixels associated with a magnification lens having a magnification from about 2 times to about 14 times with an associated focal length from about 40 millimeters to about 20 millimeters, the pixels are sized from about 2 microns and 3 microns per pixel.
 17. The system of claim 14, further comprising the pixels associated with a magnification lens having a magnification from about 5 times to about 25 times with an associated focal length from about 75 millimeters to about 38 millimeters, the pixels are sized from about 4 microns and about 6 microns per pixel.
 18. The system of claim 14, further comprising the pixels associated with a magnification lens having a magnification from about 7 times to about 38 times with an associated focal length from about 112 millimeters to about 56 millimeters, the pixels are sized from about 7 microns and about 8 microns per pixel.
 19. A method for generating a digital image, comprising: selecting optical media for generating a microscopic image of one or more specimens in an object plane, wherein the optical media defines an image plane; and adapting a sensor having a plurality of pixels to the optical media; wherein the sensor and optical media adapted together scales and projects the pixels as virtually-reduced pixels in the image plane in accordance with at least one of the following criteria: (a) the individual virtually-reduced pixels are about a size of a diffraction-limited parameter associated with the optical media; (b) the individual virtually-reduced pixels are a size of at minimum 0.1% to at maximum about the same size as a diffraction-limited parameter associated with the optical media; or (c) a diffraction-limited parameter associated with the optical media is a size of at minimum 0.1% and at maximum about the same size of the individual virtually-reduced pixels; wherein the optical media is associated with the sensor; the optical media defines in the object plane one or more of a Blur-circle, an Airy disk, and a diffraction-limited spot and one or more of a Blur-circle, an Airy disk, and diffraction-limited spot is one or more of matched, unit-mapped, correlated with the pixels; and the optical media defines that a Modulation Transfer Function of the sensor can be matched to Modulation Transfer Function of the object plane.
 20. A system for generating a digital image, comprising: means for generating a microscopic image of a specimen; means for digitally sensing the microscopic image in an infinity space; and means for performing a k-space transformation to promote a predetermined band of k-space frequencies between the specimen and the means for digitally sensing. 